Patent Grant
11744600
The field of the invention generally relates to an aspiration system for removing, by aspiration, undesired matter such as a thrombus from a fluid carrying cavity, duct, or lumen of the body, such as a blood vessel.
A treatment method for removing undesired matter such as thrombus from a blood vessel of a patient involves use of an aspiration catheter having elongate shaft formed with an aspiration lumen extending therein. An aspiration catheter may also include a guidewire lumen for placement of a guidewire, which is used to guide the aspiration catheter to a target site in the body. By applying a vacuum (i.e. negative pressure) to a proximal end of the aspiration lumen, for example, with a syringe having a hub that is connected to the proximal end of the aspiration catheter, the matter can be aspirated into an aspiration port at the distal end of the aspiration catheter, into the aspiration lumen, and thus be removed from the patient.
In one embodiment, a system for real time monitoring of catheter aspiration includes a pressure sensor configured for placement in fluid communication with a lumen which at least partially includes an aspiration lumen of a catheter, the aspiration lumen configured to couple to a vacuum source, a measurement device coupled to the pressure sensor and configured for measuring deviations in fluid pressure, and a communication device coupled to the measurement device and configured to generate a continuous signal which is proportional to measured fluid pressure.
In another embodiment, a system for real time monitoring of catheter aspiration includes a pressure sensor configured for placement in fluid communication with an aspiration lumen of a catheter, the aspiration lumen configured to couple to a vacuum source, a measurement device coupled to the pressure sensor and configured for measuring variations in fluid pressure, and a communication device coupled to the measurement device and configured to generate a continuous signal which varies proportionally as a result of variation in fluid pressure.
The present disclosure relates to aspiration catheter systems and monitoring, warning and communication systems for aspiration catheter systems. Clogging of aspiration catheters, for example by large pieces of thrombus, is a common concern for users. Techniques to avoid clogging/choking of material within the catheter often involve rapidly, aggressively advancing the aspiration catheter or gently plucking at edges of a thrombus to insure only small pieces or portions are introduced at a time, pieces which are small enough to not clog or occlude the aspiration lumen. When a device becomes clogged during use, the potential for inadvertent dislodgment of thrombus downstream increases; this is referred to as distal embolism. As aspiration procedures of this type are often used in highly technical emergent settings, early clog detection of the aspiration catheter for the user during aspiration can contribute to the success of the procedure and clinical outcome. Some sources have reported that up to 50% of aspiration catheters used get clogged during use.
The user may have difficulty determining whether there is a vacuum in the system or not. For example, the user may have difficulty determining whether the vacuum has been applied or not (e.g., the vacuum source has been turned on or off). Additionally, the user may have difficulty determining whether there has been a loss of vacuum in the system, for example because of the syringe (or other vacuum source) being full of fluid or because of a leak in the system. Blood is relatively opaque and can coat the wall of the syringe, thus making it difficult to determine when the syringe becomes full. This makes it difficult to determine whether sufficient vacuum is being applied to the aspiration catheter. The vacuum level may change to an unacceptable level even before the syringe becomes full. Extension tubing or other tubing may also cause a loss in vacuum in the system. Certain tubing kinks may be difficult for a user to see or identify. It is also difficult to determine whether there is an air leak in the system, which can be another cause for a loss of vacuum even before the syringe becomes full of the aspirated fluid.
During the aspiration of thrombus with an aspiration catheter, it is difficult to identify when thrombus is actively being aspirated, or when only blood is being aspirated. Typically, it is desired to not aspirate sizable quantities of normal blood from blood vessels, because of the importance of maintaining normal blood volume and blood pressure. However, when tracking the tip of an aspiration catheter in proximity to a thrombus, it is difficult to know whether the aspiration catheter has actively engaged a thrombus, whether it has aspirated at least a portion of the thrombus, or whether it is not engaged with the thrombus, and is only aspirating blood. Though some aspiration catheters, such as those used in the peripheral blood vessels or in an arterio-venous fistula, may be around 50 cm or even less, the tip of an aspiration catheter may in same cases be more than 90 cm from the hands of the user, or as much as 135 cm from the hands of the user, or in some cases as much as 150 cm, and the particular status of vacuum at the tip of the catheter is often not known by the user. A user may thus be essentially plunging a catheter blindly without significant, usable sensory feedback. The catheter may have an outer diameter up to or even greater than 6 French, and may be as high as 10 French or greater. The increased catheter outer diameter can cause some concern of potential trauma inside a blood vessel. The use of aspiration catheters can therefore be inefficient, and cause more blood removal than desired, causing a user to minimize the length of the therapy and in severe cases necessitating blood transfusion. An increased volume of normal blood being aspirated also means that the vacuum source (e.g. syringe) will fill in a shorter amount of time, thus requiring more frequent replacement of the vacuum source. Distal embolism may occur if the vacuum pressure is not sufficient, and yet the user is not aware.
In some cases, a syringe that is completely or mostly full or blood and/or thrombus may continue to be used, though in this state, there is not sufficient pressure to effectively aspirate thrombus or unwanted material, thus causing inefficient use of time, and lengthening the procedure. In some cases, the user may not realize the plunger of the syringe has mistakenly not been pulled back (to evacuate the syringe). In some cases, the syringe itself may be defective, and a proper vacuum may not be achieved, without the user being aware. In some cases, kinked tubing, lines, or catheters may go unnoticed, because of bad visibility in a procedural laboratory, or simply from the extent of concurrent activities being performed. In many cases, the user's eyes are oriented or focused on a monitor, for example a fluoroscopic monitor or other imaging monitor, or a monitor with patient vital data. Though the user may be able to view flow through transparent or partially transparent lumens (such as extension tubing), in dim lighting with intermittent viewing, it is difficult for the user's mind to process flow of an opaque liquid (such as blood/thrombus). Even in good lighting with a focused eye, the movement of fluid through extension tubing may not present an accurate picture of the aspiration status, as the visual flow effect may be delayed in relation to the applied vacuum. More than one medical device personnel may be sharing sensory information with each other to attempt to build a current status in each other's minds of the aspiration procedure. When a user relies on another's interpretation, especially when either are multitasking, a false sense of the status may occur. A syringe attached to the aspiration catheter may cause kinking, for example, if placed on an uneven surface. The distal opening in an aspiration lumen of an aspiration catheter may be prone to aspirating directly against the wall of a blood vessel, thus being temporarily stuck against the vessel wall, and stopping flow throughout the aspiration lumen. In some cases, a vacuum that is too large may be accidentally or inappropriately applied to the aspiration lumen of the aspiration catheter, limiting effectiveness (for example, if it causes the walls surrounding the aspiration lumen to collapse and thus, cut off the significantly decrease the flow through the aspiration lumen). The syringes which are sometimes used as a vacuum source to connect to an aspiration lumen of an aspiration catheter may malfunction, and not be fully actuated/evacuated. But, even when the syringe is functioning correctly, it will tend to fill up at difficult to predict moments, and thus commonly have periods with no applied vacuum. In the cases wherein a portion of clot/thrombus is being aspirated through the aspiration lumen, a significant pressure drop may occur at the current position of the thrombus, and thus, a sufficient vacuum may only exist from the proximal end of the aspiration lumen and distally up to the point of the thrombus. Thus, an insufficient vacuum may exist at the distal end of the aspiration lumen, e.g., at the distal end of the aspiration catheter. The same situation may occur if there is an actual clog at some intermediate point within the aspiration lumen. In either of these conditions, because of the insufficient vacuum at the distal end of the aspiration lumen, there may be a risk of thrombus or emboli being sent distally in the vasculature, which may cause occlusion, stroke, pulmonary embolism, or other disorders, depending upon the location of the intervention or procedure being performed. With current apparatus and techniques, these situations are very difficult to detect when they occur. It has been estimated that in as many as 50% of thrombus aspiration procedures, some sort of failure occurs.
An aspiration system 2 is illustrated in
The pressure transducer 12 of the aspiration monitoring system 48 is configured to be fluidly coupled between the vacuum source 6 and the aspiration catheter 4. In
For definition purposes, when speaking of the amount of vacuum, a pressure of, for example, −15,000 pascal (−2.18 pounds per square inch, or psi) is a “larger vacuum” than −10,000 pascal (−1.45 psi). Additionally, −15,000 pascal is a “lower pressure” than −10,000 pascal. Furthermore, −15,000 pascal has a larger “absolute vacuum pressure” than does −10,000 pascal, because the absolute value of −15,000 is larger than the absolute value of −10,000. In
One or more communication devices 58a, 58b, 58c are included within the aspiration monitoring system 48 and are coupled to the measurement device 54. Each of the one or more communication devices 58a-c are configured to generate a type of alert comprising an alert signal 60a-c, in response at least in part to activity and output of the measurement device 54. In some embodiments, the communication device 58a may include one or more LEDs (light emitting diodes) configured to generate a visible alert via a visible alert signal 60a, such as light that is continuously illuminated, or is illuminated in a blinking pattern. In some embodiments, the LEDs may be oriented on multiple sides of the communication device 58a, so that they may be easily seen from a variety of different locations. In some embodiments, lights other than LEDs may be used. Light pipes or other lighting conduits may also be incorporated in embodiments, to further place visual indicators at multiple locations and/or orientations. In some embodiments, the communication device 58b may include one or more vibration generators configured to generate a tactile alert via a tactile alert signal 60b, which may include, but is not limited to, vibration or heat. In some embodiments, the vibration device may be similar to a video game controller. In some embodiments, the vibration generator may comprise a piezoelectric device which is configured to vibrate when a voltage is applied. In some embodiments, the communication device 58c may include one or more sound generating devices configured to generate an audible alert via an audible alert signal 60c, such as a continuous noise, or a repeating noise. The communication device 58c in some embodiments may comprise a loudspeaker for generation of any variety of sounds, at any variety of frequencies (Hz) or sound pressures (dB) within the human audible range and/or human tolerance range. The communication device 58c may even be configured to generate sounds that are outside the human audible range in embodiments wherein the signal is intended to be felt as a vibration or other tactile sensation, instead of an audible sensation. In some embodiments, the sound generating device may comprise a buzzer which is configured to sound one or more audible pitches when a voltage is applied. In some embodiments a piezoelectric device, such as that described in relation to the communication device 58b may also serve as a sound generating device, included as communication device 58c. The alert signal 60a-c can at times serve as a “wake up” alarm for the user, in cases where the user has become too focused on other factors during the procedure.
A user of an aspiration system 2 may desire to be notified of several conditions which may occur during use of the aspiration system 2. These potential conditions include, but are not limited to clogging, a loss of vacuum due to filling of the vacuum source 6 and or a breach, break or puncture in the aspiration system 2, and the engagement or aspiration of non-fluid, solid or semi-solid material such as thrombus. The aspiration monitoring system 48 of
The pressure transducer 12 of the aspiration monitoring system 48 is configured to continuously measure and monitor the absolute pressure amplitude within the closed system of the aspiration system 2, and also is configured to measure and monitor the relative pressure over time to detect noteworthy flow changes within the flow circuit of the aspiration system 2. Some changes are discernible via absolute pressure measurement, while more subtle pressure deflections may be compared to a stored library in memory. Noteworthy conditions may be signaled to the user when appropriate. In some embodiments, the unfiltered signal may be amplified by an amplifier and filtered by a filter, for example, to increase the signal-to-noise ratio. Examples of the (background) noise 57 in an unfiltered signal can be seen in
In some embodiments, the communication device 68 may be wearable by the user.
The measurement device 54, 64 is configured to compare the curve 97 with information stored in the memory module 56, 66 to identify this condition. In some embodiments, the measurement device 54, 64 uses an algorithm to make the comparison. In some embodiments, the measurement device 54, 64 then sends a signal to the communication device 58a-c, 74, and the communication device 58a-c, 74 generates an appropriate alert. Communication device 58a, for example a particular color LED, may be illuminated, or an LED may flash in a particular pattern or number of flashes. Communication device 58b may create a characteristic sound, or may generate an audio message in a number of languages. For example, the audio message may state, “Thrombus encountered,” or “No thrombus encountered.” A different type of sound may be used for each of a plurality of “modes”: “Thrombus encountered,” “Actively flowing,” and “No Vacuum.” For example, a buzzing sound for “Thrombus encountered,” a beep for “No vacuum,” etc. The various characteristics of sound that may be varied include, but are not limited to timbre, or sound quality, spectrum, envelope, duration, phase, pitch (frequency), number of sounds (repetition). Communication device 58c may vibrate or heat in a characteristic pattern, for example, a certain number of repetitions or a certain frequency between repetitions. The user may determine that an additional fluoroscopic image (e.g. angiography) or other imaging modalities may be necessary to better identify the location of the thrombus 88.
The measurement device 54, 64 is configured to compare the curve 93 with information stored in the memory module 56, 66 to identify this condition. In some embodiments, the measurement device 54, 64 uses an algorithm to make the comparison. In some embodiments, a pre-set pressure differential ΔP1 may be stored in the memory module 56, 66 as a threshold, whereby the measurement of a pressure difference 81 less than this threshold does not result in the measurement device 54, 64 commanding the communication device 58a-c, 74 to send an alert signal 60a-c, 70. In some embodiments, when the pressure difference 81 is greater than (or greater than or equal to) the pre-set pressure differential ΔP1, the measurement device 54, 64 then sends a signal to the communication device 58a-c, 74, and the communication device 58a-c, 74 generates an appropriate alert. Communication device 58a, for example a particular color LED, may be illuminated, or an LED may flash in a particular pattern or number of flashes. Communication device 58b may create a characteristic sound, or may generate an audio message in a number of languages. For example, the audio message may state, “Clog Condition.” Communication device 58c may vibrate or heat in a characteristic pattern, for example, a certain number of repetitions or a certain frequency between repetitions. When the user realizes that the clog condition is present, the user may pull on the aspiration catheter 4 and readvance it, in an attempt to contact a portion of the thrombus 88 that can be aspirated. If a portion of the thrombus is clogged in the aspiration lumen 18, and repositioning of the aspiration catheter 4 does not produce good results, the aspiration catheter 4 can be removed and the aspiration system 2 can be repurged, for example by a positive pressurization.
The measurement device 54, 64 is configured to compare the curve 85 with information stored in the memory module 56, 66 to identify this condition. In some embodiments, the measurement device 54, 64 uses an algorithm to make the comparison. In some embodiments, the measurement device 54, 64 then sends a signal to the communication device 58a-c, 74, and the communication device 58a-c, 74 generates an appropriate alert. Communication device 58a, for example a particular color LED, may be illuminated, or an LED may flash in a particular pattern or number of flashes. Communication device 58b may create a characteristic sound, or may generate an audio message in a number of languages. For example, the audio message may state, “System Leak.” Communication device 58c may vibrate or heat in a characteristic pattern, for example, a certain number of repetitions or a certain frequency between repetitions. Upon receiving the alert, the user will check the components of the aspiration system 2 and either fix the breach or replace one or more of the components of the aspiration system 2. For example, in some cases, the communication device 58a-c, 74 may alert the user when the measurement device 54, 64 confirms a loss of vacuum, allowing the user to change or recharge the vacuum source 6, which has become depleted (e.g. by filling with blood and/or thrombus).
The measurement device 54, 64 is configured to compare the curve 79 with information stored in the memory module 56, 66 to identify when the pieces or portions 90 of thrombus 88 are actively being aspirated, as in deviation 77 and deviation 73, and when the pieces or portions of thrombus 88 are not being actively, or substantially, aspirated, as in steady pressure curve 97, the steady pressure curve 75, and the steady pressure curve 71. In some embodiments, the measurement device 54, 64 uses an algorithm to make the comparison. In some embodiments, a pre-set pressure differential ΔP2 may be stored in the memory module 56, 66 as a threshold, whereby the measurement of a pressure difference 69 less than this threshold does not result in the measurement device 54, 64 commanding the communication device 58a-c, 74 to send a first type of alert via an alert signal 60a-c, 70. In some embodiments, when the pressure difference 69 is greater than (or greater than or equal to) the pre-set pressure differential ΔP2, the measurement device 54, 64 then sends a signal to the communication device 58a-c, 74, and the communication device 58a-c, 74 generates an appropriate alert. Communication device 58a, for example a particular color LED, may be illuminated, or an LED may flash in a particular pattern or number of flashes. In some embodiments, the communication device 58a may comprise a light whose intensity increases proportionally with the pressure. Communication device 58b may create a characteristic sound, or may generate an audio message in a number of languages. For example, the audio message may state, “Thrombus being aspirated.” In some embodiments, communication device 58b may comprise one or more noises or beeps. In some embodiments, the communication device 58b may comprise a particular series of beeps corresponding to each different condition. For example, three short beeps may correspond to no thrombus being aspirated, while five long, loud beeps may correspond to a system leak. In some embodiments, a plurality of different tones (pitches) may be used to alert a user about different conditions. As an example, a low pitch sound may be used for a first condition (e.g. no thrombus being aspirated) and a second, higher pitch sound may be used for a second condition (e.g. a system leak). In some embodiments, a plurality of different tones may be used to alert a user about a first condition and a second plurality (e.g. in a different combination, or with additional tones) may be used to alert a user about a second condition. Communication device 58c may vibrate or heat in a characteristic pattern, for example, a certain number of repetitions or a certain frequency between repetitions. When the user realizes that the thrombus is being aspirated, the user may choose to advance (or retract) the aspiration catheter 4, for example with fluoroscopic visualization, along the length of the thrombus 88, in an attempt to continue the aspiration of the thrombus 88. In some cases, the user may choose to stop the advancement or retraction of the aspiration catheter 4 at a certain amount of time after the alert is generated, in order to allow the pieces or portions 90 of thrombus 88 to completely exit the aspiration lumen 18. When the measurement device 54, 64 identifies a subsequent steady pressure curve 75, 71 that follows a deviation 77, 73, the measurement device 54, 64 in some embodiments sends a signal that causes the communication device 58a-c, 74 to generate a second type of alert via an alert signal 60a-c, 70. For example, in some embodiments, communication device 58b may send an audio message that states, “Thrombus no longer being aspirated.” When the user realizes that the thrombus is no longer being aspirated, the user may advance or retract the aspiration catheter, in an attempt to contact another portion of the thrombus 88 that can be aspirated. In some embodiments, the deviation 77 may be positively identified as a true deviation indicating thrombus being actively aspirated, pressure difference 69 is between about 700 pascal and about 1700 pascal. In some embodiments, the deviation 77 may be positively identified as a true deviation indicating thrombus being actively aspirated, pressure difference 69 is between about 1000 pascal and about 1300 pascal. In some embodiments, the deviation 77 may be positively identified as a true deviation indicating thrombus being actively aspirated, pressure difference 69 is about 1138 pascal. The pressure difference 69 may be measured by determining a baseline pressure 63 and a peak pressure 61 and determining the absolute value difference. For example:
Absolute value difference (AVD)=|(−89,631 pascal)−(−90,769 pascal)|=1138 pascal
Or for example:
Absolute value difference (AVD)=|(−43,710 pascal)−(−45,102 pascal)|=1281 pascal
The pressure difference 81 (
Because vacuum pressure is a negative pressure, the peak pressure 61, as shown in
The baseline pressure 63 may in some embodiments be predetermined and may be stored in the memory module 56, 66. In some embodiments, the baseline pressure 63 may be stored in in the memory module 56, 66 during the manufacture of the aspiration monitoring system 48, 62, 78, but the baseline pressure 63 may also be input by the user prior to or during a particular procedure. In some embodiments, the baseline pressure 63 may be determined or otherwise defined by the measurement device 54, 64, 76 based on averaging of a particular number of samples of measured pressure. The baseline pressure 63 may be constructed as a moving average, such as a running average or rolling average. Several types of moving average may be used, including a simple moving average, a cumulative moving average, a weighted moving average, or an exponential moving average. In any of these cases, a threshold may be determined by the measurement device 54, 64, 76 based on the determined baseline pressure 63 and a known pressure differential ΔP. In some case, a pressure differential ΔP may even be calculated by the measurement device 54, 64, 76 based on the determined baseline pressure 63 and a known threshold.
Insertion of the pressure transducer 12 in line in either the embodiment of
In some embodiments, instead of an LED, the visual alert is provided by a communication device 58a comprising a display which displays visual messages of text in a particular language, for example, “Thrombus encountered,” “No thrombus encountered,” “Clog condition,” “System leak,” “Loss of vacuum,” “Thrombus being aspirated,” or “Thrombus no longer being aspirated.” The visual messages may be combined with any of the other alert signals 60a-c, 70 described herein. The aspiration monitoring system 48, 62, 78 described herein give real time awareness to users performing aspiration procedures, such as the removal of thrombus via an aspiration system 2. One skilled in the art will recognize that by knowing the real time condition of the aspiration system 2, the user is able to immediately make changes to the procedure in order to optimize results, increase safety for the patient and/or medical personnel, reduce costs (e.g. number of vacuum sources 6 required), and reduce procedure time (also a cost benefit). Because the user is typically performing multiple tasks during an aspiration procedure, the sensory aid provided by the aspiration monitoring system 48, 62, 78 allows the user to focus on these tasks without having to continually attempt to monitor conditions which are often difficult to visually monitor. The user may also modify and control the aspiration monitoring system 48, 62, 78 via an input 59 (
In some embodiments, alternate power sources may be used, for example, standard AC power with or without an AC/DC convertor; direct connection to existing equipment (e.g. vacuum pumps, etc.); solar power. The aspiration monitoring system 48, 62, 78 may be packaged sterile or may be resterilizable by techniques known by those skilled in the art. In some embodiments, flow or volume gauges may be used in conjunction with or instead of the pressure gauge 12, in order to determine, for example, a clog, or a change in the amount of vacuum. In some embodiments, the input 59, power module 72, measurement device 64, memory module 66, and communication device 68 (e.g., of
Though aspiration of thrombus has been described in detail, the aspiration monitoring system 48, 62, 78 has utility in any aspiration application wherein heterogeneous media is being aspirated. This may include the aspiration of emboli (including not thrombotic emboli) from ducts, vessels, or cavities of the body, or even from solid or semi-solid portions of the body, including, but not limited to, portions of fat, breasts, and cancerous tissue.
In some embodiments, the aspiration system 2 is be provided to the user as a kit with all or several of the components described, while in other embodiments, only the aspiration monitoring system 48 is provided. Though discussion herein includes embodiments for aspiration of thrombus and blood, the definition of the word “fluid” should be understood throughout to comprise liquids and gases.
In some embodiments, an additional or alternate sensor may be used to monitor flow conditions for the notification of the user, including, but not limited to: a Doppler sensor, an infrared sensor, or a laser flow detection device. In some embodiments, an externally-attached Doppler sensor may be employed. In some embodiments, an infrared sensor or a laser flow detection device may be employed around the extension tubing 10.
Additional embodiments allow real time communication of the particular value of fluid pressure (for example the level of vacuum) measured by the sensor 50. For example, as the amount of vacuum increases, an audible sound may increase in sound intensity or in sound pressure level (dB) proportionally. Or, as the amount of vacuum increases, the pitch (frequency) of an audible sound may made to rise, and as the amount of vacuum decreases, the pitch may be made to fall (as does a siren). By controlling either the amplitude of a signal or the frequency of a signal by making them proportional to the fluid pressure, the system can give a user a real-time sense of whether the vacuum is increasing, decreasing, or staying the same, as well as whether the pressure is close to zero or quite different from zero. When an audible sound is used as the signal, the user's eyes can remain focused on the procedure, whether by viewing a monitor of fluoroscopic images, the patient, or a separate piece of equipment.
Sound Pressure Level (dB)=A+B×(1/fluid pressure)
In one particular example, a modified signal curve 806 may be created that has the following mathematical relationship with the signal from the vacuum sensor 50 represented by the pressure curve 802.
Sound Pressure Level (dB)=70+20×(1/fluid pressure (kPa))
The modified signal curve 806 may be constructed of an algorithm such that the sound pressure level drops below the audible level of human hearing at relatively small amounts of vacuum, thus giving the user an “on/off” awareness of the vacuum being applied.
Sound Pressure Level (dB)=A+B×|(fluid pressure)|
In one particular example, a modified signal curve 826 may be created that has the following mathematical relationship with the signal from the vacuum sensor 50 represented by the pressure curve 822.
Sound Pressure Level (dB)=2×|(fluid pressure (kPa))|
The modified signal curve 826 may be constructed of an algorithm such that the sound pressure level seems to the user to follow the amount of vacuum being applied, thus becoming louder as the vacuum is increased.
A pressure curve 842 shows a vacuum being applied at a pressure drop 848, and a maintenance of vacuum 850a with a decrease in vacuum 852 and an increase in vacuum 854. A removal of vacuum 856 is shown at the end of the pressure curve 842. In some cases, the decrease in vacuum 852 may be caused by a temporary or permanent leak or detachment within the system or by filling of the vacuum source (e.g., syringe). In
Sound Frequency (Hz)=A+B×|(pressure)|
In one particular example, a modified signal curve 846 may be created that has the following mathematical relationship with the signal from the vacuum sensor 50 represented by the pressure curve 842.
Sound Frequency (Hz)=50×|(fluid pressure (kPa))|
The modified signal curve 846 may be constructed of an algorithm such that the sound frequency seems to the user to follow the amount of vacuum being applied. In this embodiment, the pitch of the sound becomes “higher” when vacuum is increased (fluid pressure decreases), and “lower” when the vacuum is decreased. Alternatively, the opposite may instead by chosen, wherein the pitch of the sound becomes lower when vacuum is increased.
Sound Frequency (Hz)=A+B×(fluid pressure)
In one particular example, a modified signal curve 866 may be created that has the following mathematical relationship with the signal from the vacuum sensor 50 represented by the pressure curve 862.
Sound Frequency (Hz)=40×(fluid pressure (kPa))
It should be noted that in this equation, no absolute value is used, but rather the actual value of fluid pressure. Or in some cases, an absolute (or negative) value may be used.
The modified signal curve 866 may be constructed of an algorithm such that the sound maintains a steady pitch until the clot is being sucked through the catheter, at which time the pitch changes slightly, but distinctly, away from a steady pitch. For example, in some embodiments, the pitch may change between about 20 Hz and about 2000 Hz to correspond to a pressure change of between about one kPa to about two kPa, or between about 40 Hz and about 80 Hz.
In any of the examples, the modification of signals may include any type of signal conditioning or signal modification that may be performed, including, but not limited to filtering, amplification, or isolation. The modified signal curve 806, 826, 846, 866 is used to determine the output signal to be generated by the communication device 58, 68, 74. As mentioned, if the output signal of the communication device 58, 68, 74 is configured to be an audible sound, the sound pressure level may be varied, or the sound frequency may be varied. In some embodiments, the output signal of the communication device 58, 68, 74 may have both its sound pressure level and sound frequency varied. In one embodiment, the sound frequency varies continuously in proportion to fluid pressure, but at one or more particular thresholds of fluid pressure, the sound pressure level may be caused to vary quite suddenly and strikingly. Thus there is a two-part communication occurring, a continuous real-time status indicator, with an intermittent, alert indicator (failure, danger, etc.). In some cases, the continuous real-time status indicator may represent a first continuous signal and the alert indicator may represent a second alert signal. In other cases, the continuous real-time status indicator and the alert indicator may be combined or integrated into the same signal. In some embodiments, other characteristics of psychoacoustics may be varied using variable sound generation devices. In some embodiments, the spectral envelope may be varied. In some embodiments, timbre may be changed to varies levels between light and dark, warm and harsh, or different noise “colors” (pink, white, blue, black, etc.).
Though an audible output from the communication device 58, 68, 74 has been described with the examples from
In some cases, a pseudo-continuous analog may be used in place of a truly variable output. For example, instead of a single light whose intensity is continuously varied, an array of multiple lights, for example and array comprising multiple LEDs, may be used, with an increased number of LEDs being lit when the level of vacuum is increased, and a decreased number of LEDs being lit when the level of vacuum is decreased. The same may be possible with an array comprising multiple vibrating elements, wherein more elements begin vibrating upon an increase or decrease, depending on the application, of fluid pressure.
In any of the embodiments described in relation to
Thus, a base mathematical relationship used with the proportionality described with respect to the embodiment of
Sound Pressure Level (dB)=A+B×(1/ΔP)
Likewise, a base mathematical relationship used with the proportionality described with respect to the embodiment of
Sound Pressure Level (dB)=A+B×|(ΔP)|
Likewise, a base mathematical relationship used with the proportionality described with respect to the embodiment of
Sound Frequency (Hz)=A+B×|(ΔP)|
Likewise, a base mathematical relationship used with the proportionality described with respect to the embodiment of
Sound Frequency (Hz)=A+B×(ΔP)
A pressure transducer 912 of an aspiration monitoring system 900 is illustrated in
An aspiration system 1000 in
A system for forced (or assisted) aspiration 1100 in
In an alternative embodiment, the forced aspiration catheter 1013 of the aspiration catheter 4 may have an additional lumen or guide channel for placement of an additional device or tool. In some embodiments, the guidewire lumen 26 may be used as this additional lumen, and may extend the entire length or most of the length of the catheter, so that the lumen is accessible from the proximal end 14. The additional device or tool may comprise a laser fiber, a mechanical screw, a vibrating wire or a variety of other modalities for disrupting thrombus or other material.
In any of the embodiments presented, the system may be configured so that most or all of the components are supplied together. For example, a catheter and an aspiration monitoring system that are permanently attached to each other. In some embodiments, the aspiration catheter and/or the aspiration monitoring system may include configurations that purposely make it difficult to reprocess (e.g., clean or resterilize) them, thus protecting from potential uses that are not recommended or warranted, and which may risk patient infection and/or device malfunction. For example, the sensor or the portion adjacent the sensor may be purposely difficult to access or clean. Alternatively, one or more batteries may be impossible to access or change.
In some embodiments, it may be desired to have other descriptive warnings that can be tied to pressure measurement or pressure measurement combined with another measured attribute. For example, if a sensor (accelerometer or temperature sensor) within the aspiration catheter is used to detect catheter movement, a change in this sensor may be tied to the pressure sensor. In this manner, a catheter that is engaged with a thrombus at its tip and is moved (e.g., begins to be pulled out of the patient) may then cause a warning: “Warning, do not move catheter; risk of thromboembolus.”
An interface connector 518 joins the extension tubing 514 and the catheter 516 together. In one contemplated embodiment, the interface connector 518 may contain a filter assembly 508 between high pressure fluid injection lumen 502 of the extension tubing 514 and a high pressure injection lumen 536 of the catheter 516 (
Attached to the hand piece 512 are a fluid source 520 and a vacuum source 522. A standard hospital saline bag may be used as fluid source 520; such bags are readily available to the physician and provide the necessary volume to perform the procedure. Vacuum bottles may provide the vacuum source 522 or the vacuum source 522 may be provided by a syringe, a vacuum pump or other suitable vacuum source. The filter assembly 508 serves to filter particulate from the fluid source 520 to avoid clogging of the high pressure injection lumen 536 and an orifice 542 (
In one contemplated embodiment, the catheter 516 has a variable stiffness ranging from stiffer at the proximal end to more flexible at the distal end. The variation in the stiffness of the catheter 516 may be achieved with a single tube with no radial bonds between two adjacent tubing pieces. For example, the shaft of the catheter 516 may be made from a single length of metal tube that has a spiral cut down the length of the tube to provide shaft flexibility. Variable stiffness may be created by varying the pitch of the spiral cut through different lengths of the metal tube. For example, the pitch of the spiral cut may be greater (where the turns of the spiral cut are closer together) at the distal end of the device to provide greater flexibility. Conversely, the pitch of the spiral cut at the proximal end may be lower (where the turns of the spiral cut are further apart) to provide increased stiffness. A single jacket covers the length of the metal tube to provide for a vacuum tight catheter shaft. Other features of catheter 516 are described with reference to
The operator control interface 506 is powered by a power system 548 (such as a battery or an electrical line), and may comprise an electronic control board 550, which may be operated by a user by use of one or more switches 552 and one or more indicator lamps 554. The control board 550 also monitors and controls several device safety functions, which include over pressure and air bubble detection and vacuum charge. A pressure sensor 564 monitors pressure, and senses the presence of air bubbles. Alternatively, an optical device 566 may be used to sense air bubbles. In one contemplated embodiment, the pump pressure is proportional to the electric current needed to produce that pressure. Consequently, if the electric current required by pump 526 exceeds a preset limit, the control board will disable the pump by cutting power to it. Air bubble detection may also be monitored by monitoring the electrical current required to drive the pump at any particular moment. In order for a displacement pump 526 to reach high fluid pressures, there should be little or no air (which is highly compressible) present in the pump 526 or connecting system (including the catheter 516 and the extension tubing 514). The fluid volume is small enough that any air in the system will result in no pressure being generated at the pump head. The control board monitors the pump current for any abrupt downward change that may indicate that air has entered the system. If the rate of drop is faster than a preset limit, the control board will disable the pump by cutting power to it until the problem is corrected. Likewise, a block in the high pressure lumen 536, which may be due to the entry of organized or fibrous thrombus, or a solid embolus, may be detected by monitoring the electrical current running the pump 526. In normal use, the current fluxuations of the pump 526 are relatively high. For example, the pump may be configured so that there is a variation of 200 milliAmps or greater in the current during normal operation, so that when current fluxuations drop below 200 milliAmps, air is identified, and the system shuts down. Alternatively, current fluxuations in the range of, for example, 50 milliAmps to 75 milliAmps may be used to identify that air is in the system. Additionally, an increase in the current or current fluxuations may indicate the presence of clot or thrombus within the high pressure lumen 536. For example, a current of greater than 600 milliAmps may indicate that thrombus it partially or completely blocking the high pressure lumen 536, or even the aspiration lumen 538.
A vacuum line 556, connected to the vacuum source 522, may be connected to a negative pressure sensor 558. If the vacuum of the vacuum source 522 is low or if a leak is detected in the vacuum line 556, the control board 550 disables the pump 526 until the problem is corrected. The negative pressure sensor 558 may also be part of a safety circuit 560 that will not allow the pump 526 to run if a vacuum is not present. Thereby a comprehensive safety system 562, including the safety circuit 560, the pressure sensor 564 and/or the optical device 566, and the negative pressure sensor 558, requires both pump pressure and vacuum pressure for the system to run. If a problem exists (for example, if there is either a unacceptably low pump pressure or an absence of significant vacuum), the control board 550 will not allow the user to operate the aspiration system 510 until all problems are corrected. This will keep air from being injected into a patient, and will assure that the aspiration system 510 is not operated at incorrect parameters.
When normal blood flow is achieved after unblocking occlusions or blockages from atherosclerotic lesions and/or thrombosis, there is sometimes a risk of reperfusion injury. This may be particularly significant following thrombectomy of vessels feeding the brain for treatment of thromboembolic stroke, or following thrombectomy of coronary vessels feeding the myocardium. In the case of the revascularization of myocardium following a coronary intervention (e.g. thrombectomy). Reperfusion injury and microvascular dysfunction may be mechanisms that limit significant or full recovery of revascularized myocardium. The sudden reperfusion of a section of myocardium that had previously been underperfused may trigger a range of physiological processes that stun or damage the myocardium. Distal coronary emboli, such as small portions of thrombus, platelets and atheroma, may also play a part. Controlled preconditioning of the myocardium at risk has been proposed to limit the effect of reperfusion injury and microvascular dysfunction. The embodiments of the thrombectomy systems 100, 300 presented herein may be combined with additional features aimed at allowing flow control, in order to limit the potential dangers due to reperfusion following thrombectomy. Other contemplated embodiments of an assisted aspiration system 510 which may be utilized are disclosed in U.S. Patent Application Publication No. 2010/0094201 to Mallaby (“Mallaby”) published Apr. 15, 2010, which is incorporated herein by reference in its entirety for all purposes. Other contemplated aspiration catheters are disclosed in U.S. Patent Application Publication No. 2008/0255596 to Jenson et al. (“Jenson”) published Oct. 16, 2008, which is incorporated herein by reference in its entirety for all purposes.
The multipurpose system 1200, 1240 optimizes interventional procedures, such as percutaneous coronary interventions (PCIs), for simplicity, case flow, and cost. Infusing drugs intracoronary prepares clot for aspiration by placing highly concentrated pharmaco agents directly at the lesion site, at a location which can be more distal (e.g., more superselective) than that which is typically accessible by the tip of a guiding catheter. This can minimize the volume of drug/medicant/agent used. By limiting the amount of certain medicants, systemic complications (bleeding, etc.) can be minimized or eliminated. The direct application of the medicant, for example at the thrombus itself, allows it to soften or disaggregate the thrombus. The maceration of the thrombus, for example by a saline jet 1278 (
In aspiration mode, the aspiration monitoring system 1216, 1270 is able to monitor proper function of the aspiration circuit at all times. The user knows when warnings are communicated or when the system (e.g., motor) shuts down, that a key event has occurred, an event that needs attending. This knowledge helps the user avoid plunging the catheter distally, potentially causing distal embolism. In infusion/infusate cooling mode, the pump 1254 pumps at a predetermined constant volume or speed to deliver constant temperature cooling infusate. Core temperature feedback (e.g., via rectal, esophageal, ear or other temperature probes) may be used to indicate to the system that further cooling must stop. For example, a core body temperature below 35° C. or below 34° C. The feedback of a temperature below the threshold may be used to shut down the pump and/or to send a warning. The infusate path, which is precision and direct to the catheter tip and/or ischemic area, results in concentrated cooling, causing the least systemic hypothermic potential. By bypassing the aspiration lumen (e.g., with the valve 1260 closed), unintentional embolic debris is less likely to be infused back into the blood vessel, and less likely to thus be sent downstream to critical areas. This eliminates the need to exchange devices after flow has been restored.
In some cases, in infusion mode, infusate is injected into the fluid injection lumen 1225, 1257 with a relatively low pressure. In some cases, maceration is performed at a relatively high pressure. In some cases, the multi-purpose system 1240 may be used without the pump 1254 attached, with the saline injections done by hand using a syringe attached to the infusion/injection port 1244. If a clog occurs, the syringe may be removed and the pump 1254 attached and initiated, for example, for the purpose of unclogging the injection lumen 1257. In an exemplary procedure, a user places a catheter similar to the multi-purpose catheter 1202 of
In one embodiment, an aspiration system includes an elongate catheter having a proximal end and a distal end, the catheter including an aspiration lumen having a proximal end and a distal end and a high pressure injection lumen having a proximal end and a distal end and extending from a proximal end of the catheter to a location adjacent a distal end of the aspiration lumen, and at least one orifice at or near the distal end of the high pressure injection lumen and configured to allow high pressure liquid injected through the high pressure injection lumen to be released into the aspiration lumen, wherein the proximal end of the high pressure injection lumen is configured to be repeatably coupled to and uncoupled from one or more injection modules. In some embodiments, the one or more injection modules include a first injection module and a second injection module. In some embodiments, the first injection module comprises a pump and the second injection module comprises a syringe. In some embodiments, the second injection module comprises a syringe having a volume of about 5 ml or less. In some embodiments, the second injection module comprises a syringe having a volume of about 1 ml or less. In some embodiments, the second injection module comprises a syringe containing a drug.
In one specific embodiment, an interior surface 23″ of the barrel 20″ carries one or more threads 27″ (two threads 27″ are shown in the illustrated embodiment). The threads 27″ are elongate, curved elements that may be at least partially helically oriented and configured to engage or to be engaged by cooperating features of the plunger 86″ and to cause rotational movement of barrel 20″ relative to the plunger 86″. In one particular embodiment, the threads 27″ protrude from the interior surface 23″ into the receptacle 24″ (e.g., as male threads). In another particular embodiment, the threads 27″ extend into the interior surface 23″ into the receptacle 24″ (e.g., as female threads).
An embodiment of the plunger 86″ that corresponds to the barrel 20″ may include an engagement feature 87″, such as the depicted notch, that receives and cooperates with a corresponding thread 27″, for example a male thread. In some embodiments, the engagement feature 87″ may be a protrusion which engages and cooperates with a corresponding thread 27″, for example a female thread. In a more specific embodiment, each engagement feature 87″ is formed in an alignment element 88″ of the plunger 86″. Even more specifically, each engagement feature 87″ may be formed in an edge 89″ of alignment the alignment element 88″ (illustrated as an alignment disk) of the plunger 86″. As shown, the alignment element 88″ may be located at a proximal end of the plunger 86″ (e.g., the end that will be located closest to an individual operating a syringe that includes the barrel 20″ and the plunger 86″). Edge 89″ of the alignment element 88″ may abut the interior surface 23″ of the barrel 20″ to align the plunger 86″ with the receptacle 24″ of the barrel 20″ as the plunger 86″ is forced through the receptacle 24″, along the length of the barrel 20″. As the plunger 86″ is inserted into the receptacle 24″ of the barrel 20″ and is driven axially along the length of the barrel 20″, each engagement element 87″ continues to engage its corresponding thread 27″. Due to the helical orientation of threads 27″, non-rotational movement of the plunger 86″ along the length of the barrel 20″ causes the barrel 20″ to rotate relative to the plunger 86″ as the plunger 86″ is forced through (i.e., into or out of) the receptacle 24″. In the depicted embodiment, movement of the plunger 86″ out of the receptacle 24″ (i.e., proximally, toward an individual using a syringe including the barrel 20″ and the plunger 86″) is effected as members 82″ and 84″ of handle 80″ are forced together. Members 82″ and 84″ of the handle 80″ may be rotationally joined to each other at a hinge joint 70″. In one embodiment, the barrel 20″ is rotationally and sealably held within a stationary cylindrical housing 40″ which is secured to member 82″ of the handle 80″. The barrel 20″ may be locked axially within the cylindrical housing 40″ by a snap fit, or other locking means. In another embodiment, the barrel 20″ is permanently and sealingly bonded within the cylindrical housing 40″ such that the barrel 20″ and the cylindrical housing 40″ are configured to rotate in unison. In this particular embodiment, the cylindrical housing is rotatably held by the member 82″ of the handle 80″.
Embodiments of syringes with rotatable elements and barrels 20″ that rotate relative to their plungers 86″ may be used in a variety of procedures, including, but not limited to, processes in which material (e.g., biological samples, samples from the body of a subject, aspiration of blood or thrombus/clot, etc.) is removed and/or obtained.
In a biopsy embodiment, a biopsy needle may be rigidly secured to the barrel 20″, for example at coupling element 28″. The coupling element 28″ may comprises a standard luer connector, such as a male luer lock connector. Movement of the plunger 86″ along the length of the barrel 20″ may cause the barrel 20″ and the attached biopsy needle to rotate about axes extending along their lengths, enabling use of the biopsy needle in a coring and aspiration technique to manually obtain a sample. A hand held syringe incorporating teachings of the present disclosure may be advanced and operated manually, even with a single hand, which may free the operator's other hand for a variety of purposes, including, without limitation, stabilization of a patient, control of an imaging device, such as an ultrasound apparatus, or the like.
In embodiments wherein a catheter is rigidly coupled to a barrel 20″(e.g., at the coupling element 28″) that rotates as its corresponding plunger 86″ is driven along its length, actuation of the plunger 86″ may rotate the catheter about an axis extending along its length, which may be useful in breaking up or dislodging obstructions, macerating and/or removing blood clots or thrombi, or in mixing fluids prior to or during their aspiration.
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2014/0200483 to Fojtik, published Jul. 17, 2014, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Fojtik, U.S. Patent Application Publication No. 2014/0200483, while remaining within the scope of the present disclosure.
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2004/0116873 to Fojtik, published Jun. 17, 2004, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Fojtik, U.S. Patent Application Publication No. 2004/0116873, while remaining within the scope of the present disclosure.
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2012/0022404 to Fojtik, published Jan. 26, 2012, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Fojtik, U.S. Patent Application Publication No. 2012/0022404, while remaining within the scope of the present disclosure.
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2014/0142594 to Fojtik, published May 22, 2014, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Fojtik, U.S. Patent Application Publication No. 2014/0142594, while remaining within the scope of the present disclosure.
Any of the embodiments described herein may be used conjunction with any model of the Aspire Aspiration Platform syringe (Control Medical Technology, LLC, Park City, Utah, USA), having either a rotating barrel or a non-rotating barrel.
In one embodiment, an aspiration system includes an elongate catheter having a proximal end and a distal end, the catheter including an aspiration lumen having a proximal end and a distal end, a manually-actuated syringe configured to aspirate liquid, the syringe including one or more actuation elements which control the amount of vacuum applied to the interior of the syringe and a connector configured for fluid connection, and a monitoring device including a housing having a first port adapted for detachable connection to the connector of the syringe and a second port adapted for detachable connection with the catheter, a pressure sensor in fluid communication with an interior of the housing, a measurement device coupled to the pressure sensor and configured for measuring one or more deviations in fluid pressure, and a communication device coupled to the measurement device and configured to generate a signal related to a deviation in fluid pressure measured by the measurement device.
In another embodiment, an aspiration system includes an elongate catheter having a proximal end and a distal end, the catheter including an aspiration lumen having a proximal end and a distal end, a manually-actuated syringe configured to aspirate liquid, the syringe including one or more actuation elements which control the amount of vacuum applied to the interior of the syringe and a connector configured for fluid connection, and a monitoring device including a pressure sensor in fluid communication with an interior of the syringe, a measurement device coupled to the pressure sensor and configured for measuring one or more deviations in fluid pressure, and a communication device coupled to the measurement device and configured to generate a signal related to a deviation in fluid pressure measured by the measurement device.
An aspiration system 1400 is illustrated in
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2007/0073233 to Thor et al. (“Thor”) published Mar. 29, 2007, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Thor, while remaining within the scope of the present disclosure.
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2001/0051811 to Bonnette et al. (“Bonnette”) published Dec. 13, 2001, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Bonnette, while remaining within the scope of the present disclosure.
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2014/0155931 to Bose et al. (“Bose”) published Jun. 5, 2014, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Bose, while remaining within the scope of the present disclosure.
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2010/0204672 to Lockhart et al. (“Lockhart”) published Aug. 12, 2010, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Lockhart, while remaining within the scope of the present disclosure.
Any of the embodiments described herein may include some or all features of any of the embodiments described in U.S. Patent Application Publication No. 2007/0225739 to Pintor et al. (“Pintor”) published Sep. 27, 2007, which is incorporated herein by reference in its entirety for all purposes; in addition, any of the features described herein may be incorporated into any of the embodiments described in Pintor, while remaining within the scope of the present disclosure.
While the foregoing is directed to embodiments of the present disclosure, other and further embodiments may be devised without departing from the basic scope thereof.
This application is a continuation of U.S. patent application Ser. No. 15/245,124, filed Aug. 23, 2016, now U.S. Pat. No. 10,702,292, which claims the benefit of priority to U.S. Provisional Application No. 62/211,637, filed on Aug. 28, 2015, U.S. Provisional Application No. 62/213,385, filed on Sep. 2, 2015, U.S. Provisional Application No. 62/239,795, filed on Oct. 9, 2015, U.S. Provisional Application No. 62/239,953, filed on Oct. 11, 2015, and U.S. Provisional Application No. 62/318,388, filed on Apr. 5, 2016, all of which are herein incorporated by reference in their entirety for all purposes. Priority is claimed pursuant to 35 U.S.C. § 120 and 35 U.S.C. § 119
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| Parent | 15245124 | Aug 2016 | US |
| Child | 16883094 | US |
